Logarithmic Amplifier, Electrosurgical Generator Including Same, and Method of Controlling Electrosurgical Generator Using Same

ABSTRACT

An electrosurgical generator includes an RF output stage, a current sensor, a voltage sensor, first and second log amplifiers, and a controller. The RF output stage is configured to supply electrosurgical energy to tissue. The current sensor is configured to sense a current of the electrosurgical energy and generate a current signal corresponding to the current of the electrosurgical energy. The first log amplifier is configured to amplify and compress the current signal. The voltage sensor is configured to sense a voltage of the electrosurgical energy and generate a voltage signal in response thereto. The second log amplifier is configured to amplify and compress the voltage signal. The controller is configured to receive the amplified voltage signal and the amplified current signal and operatively control the generation of the electrosurgical energy as a function of the amplified voltage signal and the amplified current signal.

BACKGROUND

1. Technical Field

The present disclosure relates to electrosurgery. More particularly, the present disclosure relates to a logarithmic amplifier, an electrosurgical generator including the same, and a method of controlling an electrosurgical generator using the same.

2. Discussion of Related Art

Electrosurgery is the application of electricity and/or electromagnetic energy to cut, dissect, ablate, coagulate, cauterize, seal or otherwise treat biological tissue during a surgical procedure. Generally, electrosurgery utilizes an electrosurgical generator operable to output energy and active and return electrodes that are electrically connected via a cable assembly to the generator. The electrosurgical generator generates an electromagnetic wave (referred to herein as “electrosurgical energy”), typically above 100 kilohertz, between the active and return electrodes when applied to tissue. The electromagnetic wave created therebetween dissipates energy as heat as it travels between the electrodes. The electrosurgical energy usually has a frequency above 100 kilohertz to avoid muscle and/or nerve stimulation.

During electrosurgery, current generated by the electrosurgical generator is conducted through the patient's tissue disposed between the two electrodes. The current causes the tissue to heat up as the electromagnetic wave overcomes the tissue's impedance. Although many other variables affect the total heating of the tissue, usually more current density correlates to increased heating.

A variety of types of instruments utilizing electromagnetic radiation have been employed for various types of monopolar and bipolar electrosurgery. The basic purpose of both monopolar and bipolar electrosurgery is to produce heat to achieve the desired tissue/clinical effect. In monopolar electrosurgery, devices use an instrument with a single, active electrode to deliver energy from an electrosurgical generator to tissue, and a patient return electrode or pad that is attached externally to the patient (e.g., a plate positioned on the patient's thigh or back) as the means to complete the electrical circuit between the electrosurgical generator and the patient. When the electrosurgical energy is applied, the energy travels from the active electrode, to the surgical site, through the patient and to the return electrode. In bipolar electrosurgery, both the active electrode and return electrode functions are performed at the site of surgery. Bipolar electrosurgical devices include two electrodes that are located in proximity to one another for the application of current between their surfaces. Bipolar electrosurgical current travels from one electrode, through the intervening tissue to the other electrode to complete the electrical circuit. Bipolar instruments generally include end-effectors, such as grippers, cutters, forceps, dissectors and the like.

Electrosurgical generators apply various currents, voltages and frequencies to achieve various tissue effects. The current, voltage, and frequency may be varied to achieve a target tissue impedance, a target power, a target voltage, and the like. These target values are generally based upon the surgical procedure to be performed, tissue characteristics, and/or the desired tissue/clinical effect. Electrosurgical generators employ one or more control systems to achieve these target values and to prevent the electrosurgical generator from operating outside predetermined constraints.

SUMMARY

Electromagnetic energy is generally classified by increasing energy or decreasing wavelength into radio waves, microwaves, infrared, visible light, ultraviolet, X-rays and gamma-rays. As it is used in this description, “transmission line” generally refers to any transmission medium that can be used for the propagation of signals from one point to another.

Although the following description describes the use of logarithmic amplifiers to compress a large output range of a generator to a small feedback range, the teachings of the present disclosure may also apply to a variety of applications where signals of large dynamic range may be encountered.

According to an aspect, a control system for controlling a generator is provided. The control system includes a sensor, a log amplifier, and a controller. The sensor generates a sensor signal. The sensor may be a voltage sensor or a current sensor. The log amplifier is coupled to the sensor and amplifies the sensor signal. The controller generates an output signal as a function of the amplified sensor signal. In some aspects, the control system further includes a summer to sum a setpoint and the negation of the amplified signal from the log amplifier. The controller may be adapted to generate electrosurgical energy, i.e., the output signal may be electrosurgical energy. The generator may be an electrosurgical generator. The electrosurgical generator may be a portable electrosurgical generator coupled to a portable surgical instrument. In other embodiments, the generator may be an ultrasonic generator or a microwave generator.

In any of the aspects, the control system includes a summer. The summer sums a setpoint and a negation of the amplified signal from the log amplifier to generate an error. The controller may generate the output signal as a function of the error.

In any of the aspects, the control system includes a voltage sensor having a plurality of capacitors. The plurality of capacitors forms a voltage divider network that is in electrical communication with the output signal. The sensor signal may be a voltage of a capacitor of the divider network.

According to another aspect of the present disclosure, the controller is a proportional-integral-derivative controller. The proportional-integral-derivative controller may have one or more variable gain coefficients. The proportional-integral-derivative controller can vary a proportional gain coefficient, an integral gain coefficient, and a derivative gain coefficient. One or more gain coefficients may be varied as a function of the amplified sensor signal. The controller may convert the amplified sensor signal to an RMS value or to an antilog of the amplified sensor signal.

In any of the aspects, an electrosurgical generator includes an RF output stage, a current sensor, first and second log amplifiers, a voltage sensor and a controller. The RF output stage supplies electrosurgical energy to tissue. The current sensor senses a current of the electrosurgical energy. The voltage sensor senses a voltage of the electrosurgical energy. The first log amplifier amplifies the current signal. The second log amplifier amplifiers the voltage signal. The controller receives the amplified voltage and current signals. The controller may be configured to control the generation of the electrosurgical energy as a function of the amplified voltage signal and/or the amplified current signal.

In any of the aspects, the controller may be configured to calculate the sum of a log voltage signal and a log current signal to compute a measured log power. The controller may be further configured to compare the measured log power against a target log power to compute an error signal.

In any of the aspects, the electrosurgical generator may include a plurality of capacitors forming a capacitor divider network coupled to the RF output stage for measuring voltage of the electrosurgical energy.

In any of the aspects, voltage sensor may include a plurality of capacitors that form a capacitor divider network. The capacitor divider network is in electrical communication with the electrosurgical energy. Additionally or alternatively, the capacitor divider network may be coupled to the RF output stage.

In any of the aspects, the electrosurgical generator may include a dual directional coupler adapted for measurement of forward and reflective voltage.

In any of the aspects, the controller is a proportional-integral-derivative controller. The proportional-integral-derivative controller may employ one or more variable gain coefficients. The proportional-integral-derivative controller may be configured to vary a proportional gain coefficient, an integral gain coefficient, and/or a derivative gain coefficient. The proportional-integral-derivative controller may include one or more look-up tables to vary one or more gain coefficients. One or more gain coefficients may be determined using an affine algorithm. In any of the aspects, a measured log power may be compared against a target log power to compute an error signal used by the proportional-integral-derivative controller.

In any of the aspects, a gain coefficient may be varied as a function of the amplified voltage signal and/or the amplified current signal. The proportional-integral-derivative controller may have a setpoint of log power, log impedance, log current, or log voltage. The controller may be configured to calculate the log power by adding the amplified log current signal to the amplified log voltage signal. The controller may be configured to calculate log impedance by subtracting the amplified log current signal from the amplified log voltage signal. The electrosurgical generator may operate without calculating an antilog, e.g., the gain coefficients may change based upon a log power or a log impedance.

According to an aspect of the present disclosure, a method of controlling an electrosurgical generator is provided. The method includes the initial steps of supplying electrosurgical energy to tissue, determining a current of the electrosurgical energy, and determining a log of the determined current of the electrosurgical energy, determining a voltage of the electrosurgical energy. The method further includes the steps of determining a log of the determined voltage of the electrosurgical energy, and controlling the electrosurgical energy as a function of the log of the determined current and the log of the determined voltage.

The method may further include the steps of applying a proportional-integral-derivative transfer function using the log of the determined current, the log of the determined voltage, a log impedance, and/or a log power. The method may further include the steps of adjusting the electrosurgical energy as a function of the applied proportional-integral-derivative transfer function, and adjusting a gain coefficient of the proportional-integral-derivative transfer function. The proportional-integral-derivative transfer function may be applied to a comparison between a setpoint and one of the log of the determined current, the log of the determined voltage, the log impedance, and the log power (e.g., feedback is subtracted from the setpoint to provide an error signal).

BRIEF DESCRIPTION OF THE DRAWINGS

Objects and features of the presently-disclosed logarithmic amplifier, electrosurgical generator including the same, and a method of controlling an electrosurgical generator using the same will become apparent to those of ordinary skill in the art when descriptions of various embodiments thereof are read with reference to the accompanying drawings, of which:

FIG. 1 shows an illustration of an electrosurgical system having an electrosurgical generator that uses logarithmic amplifiers in accordance with an embodiment of the present disclosure;

FIG. 2 shows a block diagram of the electrosurgical generator of FIG. 1 that uses logarithmic amplifiers in accordance with an embodiment of the present disclosure;

FIG. 3 shows a block diagram of the control system of the electrosurgical generator of FIG. 2 in accordance with an embodiment of the present disclosure;

FIG. 4A shows a capacitor divider network for measuring current in accordance with an embodiment of the present disclosure;

FIG. 4B shows a capacitor divider network for measuring voltage in accordance with an embodiment of the present disclosure;

FIG. 5 shows a sensor configuration for a microwave generator in accordance with an embodiment of the present disclosure; and

FIG. 6 shows a flow chart diagram of a method for controlling an electrosurgical generator using logarithmic amplifiers in accordance with an embodiment the present disclosure.

DETAILED DESCRIPTION

Hereinafter, embodiments of a logarithmic amplifier, an electrosurgical generator including the same, and a method of controlling an electrosurgical generator using the same of the present disclosure are described with reference to the accompanying drawings. Like reference numerals may refer to similar or identical elements throughout the description of the figures. In the following description, well-known functions or constructions are not described in detail to avoid obscuring the present disclosure in unnecessary detail.

Various embodiments of the presently-disclosed logarithmic amplifier are suitable for use in electrosurgical generators and electrosurgical systems including the same. The presently-disclosed logarithmic (log) amplifier embodiments can be used to amplify and compress a signal which varies over a large dynamic range into a suitable log amplifier output range, e.g., 0 volts to about 3 volts.

FIG. 1 shows an illustration of a bipolar and monopolar electrosurgical system 100 in accordance with an embodiment of the present disclosure. The electrosurgical system 100 includes a generator 102 that uses one or more logarithmic amplifiers (described below).

In some embodiments, the generator 102 is an electrosurgical generator adapted to supply electrosurgical energy to tissue, e.g., to meet the needs of the surgeon or surgical team for hospital, surgery center, and/or office-based procedures. The generator 102 may be adapted for use to perform monopolar and/or bipolar electrosurgical procedures including vessel-sealing procedures and/or other procedures. The generator 102 may include a plurality of outputs (e.g., terminals 104 and 106) for interfacing with various electrosurgical instruments (e.g., a monopolar active electrode 108, a return pad 110, bipolar electrosurgical forceps 112, a footswitch (not shown), etc.). The generator 102 may additionally, or alternatively, include electronic circuitry that is configured to generate radio-frequency power (or other type of surgical energy, e.g., light energy, microwave energy, ultrasonic energy, etc.) specifically suited for various electrosurgical modes (e.g., cutting, blending, division, etc.) and procedures (e.g., monopolar treatment, bipolar treatment, vessel sealing, etc.). The generator 102 may have a power range. In some embodiments, the generator 102 may have a power range from about 1 milliwatt (mW) (1×10⁻³ watts) to about 150 kilowatts (kW) (1×10³ watts).

The system 100 includes a monopolar electrosurgical instrument 114 having one or more electrodes 108 for treating tissue of a patient (e.g., electrosurgical pencil, electrosurgical cutting probe, ablation electrode(s), etc.). Electrosurgical RF energy is supplied to the instrument 114 by the generator 102 via a transmission line, e.g., supply line 116. As mentioned above, “transmission line” generally refers to any transmission medium that can be used for the propagation of signals from one point to another. Supply line 116 is operably connected to an active terminal 104 of the generator 102, allowing the instrument 114 to coagulate, ablate, or otherwise treat tissue. The energy is returned from electrode 108 through tissue to the generator 102 via a transmission line, e.g., via a return line 118 of the return pad 110, at a return terminal 106 of the generator 102. The active terminal 104 and the return terminal 106 may include connectors (not shown) configured to interface with plugs (not shown) of the instrument 114 and the return electrode 110, which are disposed at the ends of the supply line 116 and the return line 118, respectively.

The system 100 includes return electrodes 120, 122 within return pad 110 that are arranged to minimize the chances of tissue damage by maximizing the overall contact area with the patient's tissue. The generator 102 and the return electrode 110 may additionally, or alternatively, be configured for monitoring contact quality to ensure that sufficient contact exists therebetween to further minimize chances of tissue damage.

The system 100 generally includes a bipolar electrosurgical forceps instrument 112 having one or more electrodes (e.g., electrodes 124 and 126) for treating tissue of a patient. In some embodiments, as shown in FIG. 1, the instrument 112 includes opposing jaw members 134, 136 having an active electrode 124 and a return electrode 126 disposed therein, respectively. The active electrode 124 and the return electrode 126 are connectable to the generator 102 through a transmission line 128, e.g., a cable that includes a supply line 130 and a return line 132 coupled to the active terminal 104 and the return terminal 106, respectively. The instrument 112 is coupled to the generator 102 at a connector having connections to the active terminal 104 and the return terminal 106 (e.g., pins) via a plug (not shown) disposed at the end of the transmission line 128, wherein the plug includes contacts from the supply line 130 and the return line 132.

The generator 102 may be any suitable type (e.g., electrosurgical, microwave, etc.) and may include a plurality of connectors to accommodate various types of electrosurgical instruments (e.g., instrument 114, electrosurgical forceps 112, etc.). The generator 102 may be configured to operate in a variety of modes such as ablation, monopolar and bipolar cutting, coagulation, and other modes. The generator 102 may include a switching mechanism (e.g., relays) to switch the supply of energy, e.g., RF energy, between the connectors, such that, for instance, when the instrument 114 is connected to the generator 102, only the monopolar plug receives RF energy. The active terminal 104 and return terminals 106 may be coupled to a plurality of connectors (e.g., inputs and outputs) of the generator 102 to power a variety of instruments.

The generator 102 may include a user interface, e.g., configured to provide user-input capabilities and/or capabilities for simplified use and/or programming of the generator 102. The generator 102 includes suitable input controls (e.g., buttons, activators, switches, touch screen and the like) adapted to enable a user to selectively configure one or more operating parameters of the generator 102, or component thereof, e.g., depending upon a particular purpose and/or to achieve a desired surgical outcome. In addition, the generator 102 may include one or more display screens, such as a flat-panel display, e.g., an LCD (liquid crystal display), plasma display panel (PDP), organic light emitting diode (OLED), or electro-luminescent display (ELD), for providing the user with a variety of output information (e.g., intensity settings, treatment complete indicators, etc.). The controls allow the user to adjust power of the RF energy, waveform, and/or other parameters to achieve the desired waveform suitable for a particular task (e.g., coagulating, tissue sealing, intensity setting, etc.). The instruments 112, 114 may also include a plurality of input controls that may be redundant with certain input controls of the generator 102. Placing the input controls at the instruments 112, 114 allows for easier and faster modification of RF energy parameters during the surgical procedure without requiring user interaction with the generator 102.

Referring to the drawings, FIG. 2 shows a block diagram of the electrosurgical generator 102 of FIG. 1 in accordance with an embodiment of the present disclosure. Electrosurgical generator 102 includes a controller 200, a high-voltage power supply 202 (HVPS), a radio-frequency (RF) output stage 204, and log amplifiers 206, 208. The controller 200 includes a processor unit 210 and a memory 212. The processor unit 210 may include any type of computing device, computational circuit, or any type of processor or processing circuit capable of executing a series of instructions that are stored in a computer-readable storage medium (e.g., memory 212), which may be any device or medium that can store code and/or data. In some embodiments, the processor unit 210 may be any suitable microcontroller, microprocessor (e.g., Harvard or Von Neumann architectures), PLD, PLA, or other suitable digital logic. In some embodiments, the memory 212 may be volatile, non-volatile, solid state, magnetic, or other non-transitory computer-readable medium.

The controller 200 may include various circuitry (e.g., amplifiers, buffers, and the like) to interface the processor unit 210 to circuitry within the electrosurgical generator 102. The controller 200 receives various feedback signals that are analyzed by the processor unit 210 to provide control signals in response thereto. The control signals from the controller 200 control the HVPS 202 and the RF output stage 204 to provide electrosurgical energy to tissue, which is represented by a load R_(L) 216.

The HVPS 202 includes a power circuit 214. The power circuit 214 supplies a suitable electric current to the RF output stage 204. The RF output stage 204 converts the current from the power circuit 208 to electrosurgical energy for application to the load R_(L) 216. In some embodiments, the HVPS 202 provides a DC signal to the RF output stage 204, which, in turn, generates the electrosurgical energy using a push-pull transistor configuration coupled to a primary side of a step-up transformer (not shown).

As previously mentioned, the controller 200 receives feedback from various feedback signals that are analyzed by the processor unit 210 to provide control signals in response thereto. The controller 200 may receive a log current from the log amplifier 206 and/or a log voltage from the log amplifier 208. In some embodiments, the controller 200 receives a current signal from a current sensor 218 after amplification by the log amplifier 206. The controller 200 may additionally, or alternatively, receive a voltage signal from a voltage sensor 220 after amplification by the log amplifier 208.

Log amplifiers 206, 208 may be log amplifiers that saturate with negative input, and/or may be output polarity independent of input polarity (e.g., a detecting log amp). Log amplifiers 206, 208 may additionally, or alternatively, be true log amplifiers (e.g., may have a symmetrical response to positive or negative signals). Additionally or alternatively, the log amplifiers 206 and 208 may be successive detection log amplifiers.

The controller 200 receives the log current and log voltage signals from log amplifiers 206 and 208, respectively, and controls the high-voltage power supply 202 in response thereto. In some embodiments, the controller 200 may be a proportional-integral-derivate controller (“PID controller”).

The controller 200 may be adapted to control the output of the electrosurgical generator 102 to achieve a target log voltage, a target log current, a target power, a target log power, and/or a target log impedance, e.g., a target log tissue impedance. The controller 200 may be configured to calculate log power by adding the amplified log current signal from the log amplifier 206 to the amplified log voltage signal from the log amplifier 208. The controller 200 may be configured to calculate the log impedance by subtracting the log current signal received from the log amplifier 206 from the log voltage signal received from the log amplifier 208. In some embodiments of the present disclosure, the controller 200 converts an amplified signal from the log amplifier 206 and/or the log amplifier 208 to an RMS value or an antilog of the amplified sensor signal. In other embodiments of the present disclosure, the controller 200 does not calculate an antilog of either of the signals from the log amplifier 206 or the log amplifier 208.

The controller 200 may have one or more variable gain coefficients, e.g., a PID controller may vary one or more of a proportional gain coefficient, an integral gain coefficient, or an integral gain coefficient. In some embodiments, the one or more coefficients may be varied based upon a log current, a log voltage, a log impedance, and/or a log power.

FIG. 3 shows a block diagram of the control system 300 of the electrosurgical generator of FIG. 2 in accordance with an embodiment of the present disclosure. The control system 300 includes a summer 302, a PID transfer function 304, a PID coefficient table 306, feedback 308, and a setpoint 310.

In some embodiments, the summer 302, the RID transfer function 304, the PID coefficient table 306, the feedback 308, and the setpoint 310 are implemented by an operative set of processor executable instructions configured to be executed by at least one processor 210 within memory 212 (see FIG. 2). The memory 212 is a non-transitory computer readable (e.g., readable by processor unit 210) medium. In other embodiments, the summer 302, the PID transfer function 304, the RID coefficient table 306, the feedback 308 and the setpoint 310 may be implemented in software, hardware, software in execution, firmware, bytecode, microcode, PLDs, FPGAs, PALs, a microprocessor, a microcontroller, or some combination thereof.

The setpoint 310 may be a target log voltage, log current, log impedance, log power, or the like. Additionally or alternatively, the setpoint 310 may be a target voltage, current, power, or impedance.

The setpoint 310 is provided to summer 302. The summer 302 compares the setpoint 310 to the feedback 308. The setpoint 310 may be a desired or target value, and the feedback 308 provides the actual value being delivered to the load R_(L) 216.

The feedback 308 corresponds to the setpoint 310. For example, if the setpoint 310 is a target log voltage, then the feedback 308 provides the signal from the amplifier 208, which is the log voltage from load R_(L) 216.

The feedback 308 may calculate log power by adding the amplified log current signal received from the log amplifier 206 to the amplified log voltage signal received from the log amplifier 208. The feedback 308 may calculate the log impedance by subtracting the log current signal received from the log amplifier 206 from the log voltage signal received from the log amplifier 208. In some embodiments of the present disclosure, the feedback 308 converts an amplified signal from the log amplifiers 206, 208 to an RMS value or an antilog of the amplified sensor signal. In other embodiments of the present disclosure, the feedback 308 does not calculate an antilog from either of the signal from the log amplifiers 206 or the signal from the log amplifier 208. As previously mentioned, the feedback 308 is provided to the summer 302.

The summer 302 compares the setpoint 310 to the feedback 308 and generates an error signal. The error signal is the difference between the setpoint 310 and the feedback 308. Typically, the summer subtracts the feedback from the setpoint 310 (also referred to as negative feedback). The error signal is fed into the PID transfer function 304.

The PID transfer function 304 adds proportional, integral, and derivative terms together and outputs the results to the load R_(L) 216. Each term includes a coefficient. In some embodiments, the proportional term is the error signal multiplied by a proportional coefficient, the integral term is the integration of the error signal multiplied by an integral coefficient, and the derivative term is the derivative of the error signal multiplied by a derivative coefficient. In some embodiments, the proportional, integral and derivative terms are added together and applied to the load R_(L) 216. Although FIG. 3 shows the output of the PID transfer function 304 as being directly applied to the load R_(L) 216, various driver circuitry may be used (e.g., an analog-to-digital converter (not shown), the HVPS 202 and/or the RF output stage 203 as shown in FIG. 2).

The PID coefficients (also referred to as RID gain coefficients) are stored within the PID coefficients table 306. The PID coefficients table 306 provides the PID coefficients to the PID transfer function 304. The PID coefficients table 306 can vary one or more coefficients of the PID transfer function 304 based upon the error signal from the summer 302, a signal from the log amplifiers 206, 208, a log voltage, a log current, a log power, a log impedance, and the like. Additionally or alternatively, the PID coefficients from table 306 may be varied as a function of the voltage, current, power, of the electrosurgical energy as applied to the load R_(L) 216, or the impedance of the load R_(L) 216 (e.g., tissue impedance).

In some embodiments, the PID coefficients table 306 may have three ranges for log power with each range having three different PID gain coefficients, and the PID coefficients table 306 may load the PID gain coefficients in accordance with the current power range of the log power.

FIG. 4A shows a capacitor divider network 400 for measuring current in accordance with an embodiment of the present disclosure. The network 400 includes a configuration of capacitors 402, 404, 406, 408, 410. Referring to FIGS. 2 and 4, the capacitor 402 is coupled between the nodes 412, 414. The nodes 412, 414 may be coupled between the terminal 104 and ground, respectively, to measure the voltage applied to the load R_(L) 216. The capacitor 402 is used as a current sense element. As current goes through the capacitor 402, it produces a voltage V, which may be expressed as

${V = \frac{I \cdot {dt}}{C}},$

where I is the current, dt is the switching time of the RF stage 428 and C is the capacitance value 402. The capacitor 402 may be used as the low-frequency blocking capacitor for safety standards.

Additionally or alternatively, the nodes 412, 414 may be coupled between the terminals 104, 106, respectively, to measure the current applied to load R_(L) 216 (see FIG. 2). The current through the capacitor 402 may be derived by measuring the voltage across the capacitor 402 when the capacitance of the capacitor 402 is known or measured.

In some embodiments, as shown in FIG. 4A, the capacitors 402, 404, 406, 408, 410 are arranged in an H configuration and function as a capacitor divider network. The capacitors 404 and 408 are used for isolating the ground of the RF stage 426 from the non-isolated ground 427 of the system. The capacitors 406 and 410 are used to reduce the signal level I_(X) going to the log amplifier and reference the signal to the system ground 427.

In some embodiments of the present disclosure, optocouplers and/or isolation transformers are used to provide an isolation barrier between the patient and the ground of the generator. The component for sensing current 402 may be the current sensor 218 (FIG. 2). The components for sensing voltage 419, 421, 422, 423 may be the voltage sensor 220 that is electrically coupled to the RF output stage 204. The log amplifier 206 measures the voltage difference between the nodes of: (1) the node 418 between capacitors 404 and 406; and (2) the node 420 between capacitors 408 and 410. The capacitor 402 may be split into various parallel or serial capacitors, e.g., to adjust creepage, clearance, and voltage breakdown for the isolation barrier between the patient and ground. The divider network 400 formed by the capacitors 404, 406, 408, 410 reduces the voltage measured by the log amplifier 206 by a predetermined amount and is a function of the frequency of the electrosurgical energy and the capacitance of the capacitors 402, 404, 406, 408, 410. The capacitors 402, 404, 406, 408, 410 provide isolation between a ground of the electrosurgical generator 102 (see FIG. 2) and the patient P, e.g., to prevent voltage breakdown of the several capacitors 402, 404, 406, 408, 410 during typical use between the patient and a ground of the electrosurgical generator 102.

In some embodiments of the present disclosure, a transformer (not shown) may be interposed between the capacitor 402 and the log amplifier 206 to provide isolation therebetween and/or to step-down the voltage of the electrosurgical energy prior to measurement by the log amplifier 206.

FIG. 4B shows a capacitor divider network 410 for measuring voltage in accordance with an embodiment of the present disclosure. FIG. 4B shows the isolation of the ground 426 of the RF output stage 428 to the system ground 427 through the capacitors 419 and 422. The capacitors 419 and 422 transfer the voltage across the isolation boundary. The capacitors 421 and 423 reduce the signal level V_(X1) and V_(X2) going to the log amplifier 208 and reference the voltage to system ground 427. The active output 424 of the generator and the return output 425 of the generator are connected to the patient, represented as R_(L) 429. The two voltages V_(X1) and V_(X2) can fully monitor the output voltage across the patient and serve as redundant sensors.

FIG. 5 shows a sensor configuration 500 for a microwave generator in accordance with an embodiment of the present disclosure that provides a dual directional coupler suitable for measurement of forward and reflective voltage. The sensor configuration 500 includes a first line L₁ defined between a node 543 and the system ground 427, a second line L₂ defined between nodes 541 and 540, and a third line L₃ defined between a node 542 and system ground 427

The output 541 of a generator 540 is a coupled line that measures the forward voltage and 543 measures the reflective voltage 542. Termination resistors 544 and 545 are provided for the signal lines L₁ and L₃, respectively. The space between the lines L₁ and L₂ and the space between the lines L₂ and L₃ determines the signal strength going to the log amplifier. This signal strength is also influenced by the length of the lines for nodes L₁ and L₂, the termination resistance 444, 445, and the width of traces for lines L₁ and L₂.

FIG. 6 shows a flow chart diagram of a method 600 for controlling an electrosurgical generator using a log amplifier in accordance with an embodiment the present disclosure. Method 600 includes steps 602-620. In step 602, electrosurgical energy is supplied to tissue.

In step 604, the current of the electrosurgical energy is determined. In step 606, the log of the determined current of the electrosurgical energy is determined. For example, Step 606 may use the log amplifier 206 of FIG. 2.

In step 608, the voltage of the electrosurgical energy is determined. In step 610, the log of the determined voltage of the electrosurgical energy is determined. Step 608 may use the log amplifier 208 of FIG. 2.

Step 612 includes steps 614 through 620. Step 612 controls the electrosurgical energy as a function of the log of the determined current and the log of the determined voltage. In step 614, a gain coefficient of the proportional-integral-derivative transfer function (“PID transfer function”) is adjusted. The PID transfer function of method 600 may be the PID transfer function 304 of FIG. 3. In step 616, a PID transfer function is applied using one or more of the log of the determined current, the log of the determined voltage, a log impedance, and a log power.

In step 618, the PID transfer function is applied to an error generated by comparing a setpoint to one or more of the determined current, the log of the determined voltage, the log impedance, and the log power. Steps 616 and 618 may be integrated together or may be separate.

In step 620, the electrosurgical energy is adjusted as a function of the applied RID transfer function. Thereafter, a manual or automatic deciding step is included in step 622 to determine whether to repeat the method 600 or to stop the application of the electrosurgical energy to tissue. In some embodiments, a pressed button on a portable electrosurgical generator causes the method 600 to repeat until the button is released, then the method 600 will stop; that is, the released button causes method 600 to stop.

Although embodiments have been described in detail with reference to the accompanying drawings for the purpose of illustration and description, it is to be understood that the inventive processes and apparatus are not to be construed as limited thereby. It will be apparent to those of ordinary skill in the art that various modifications to the foregoing embodiments may be made without departing from the scope of the disclosure. 

What is claimed is:
 1. A control system for controlling an electrosurgical generator, comprising: a sensor to generate a sensor signal; a log amplifier coupled to the sensor to amplify and compress the sensor signal; and a controller to generate an output signal as a function of the amplified sensor signal.
 2. The control system according to claim 1, further comprising a summer to sum a setpoint and a negation of the amplified signal from the log amplifier to generate an error, wherein the controller generates the output signal as a function of the error.
 3. The control system according to claim 1, wherein the controller is adapted to generate electrosurgical energy thereby defining the output signal.
 4. The control system according to claim 1, wherein the sensor comprises a plurality of capacitors forming a voltage divider network coupled to the output signal, wherein the sensor signal includes a voltage of a capacitor of the divider network.
 5. The control system according to claim 1, wherein the controller is a proportional-integral-derivative controller.
 6. The control system according to claim 5, wherein the proportional-integral-derivative controller has at least one variable gain coefficient.
 7. The control system according to claim 5, wherein the proportional-integral-derivative controller varies a proportional gain coefficient, an integral gain coefficient and a derivative gain coefficient.
 8. An electrosurgical generator, comprising: an RF output stage configured to supply electrosurgical energy to tissue; a current sensor configured to sense a current of the electrosurgical energy, wherein the current sensor generates a current signal corresponding to the current of the electrosurgical energy; a first log amplifier configured to amplify and compress the current signal; a voltage sensor configured to sense a voltage of the electrosurgical energy and generate a voltage signal in response thereto; a second log amplifier configured to amplify and compress the voltage signal; and a controller configured to receive the amplified and compressed voltage signal and the amplified and compressed current signal and control the generation of the electrosurgical energy as a function of the amplified and compressed voltage signal and the amplified and compressed current signal.
 9. The electrosurgical generator according to claim 8, wherein the controller calculates a sum of a log voltage signal and a log current signal to compute a measured log power.
 10. The electrosurgical generator according to claim 8, further comprising a capacitor divider network for measuring the current of the electrosurgical energy.
 11. The electrosurgical generator according to claim 8, wherein the voltage sensor comprises a plurality of capacitors forming a capacitor divider network coupled to the RF output stage for measuring the voltage of the electrosurgical energy.
 12. The electrosurgical generator according to claim 8, further comprising a dual directional coupler adapted for measurement of forward and reflective voltage.
 13. The electrosurgical generator according to claim 8, wherein the controller is a proportional-integral-derivative controller.
 14. The electrosurgical generator according to claim 13, wherein the proportional-integral-derivative controller has at least one variable gain coefficient.
 15. The electrosurgical generator according to claim 13, wherein the proportional-integral-derivative controller varies a proportional gain coefficient, an integral gain coefficient and a derivative gain coefficient.
 16. The electrosurgical generator according to claim 13 wherein at least one gain coefficient varies as a function of at least one of the amplified voltage signal and the amplified current signal.
 17. A method of controlling an electrosurgical generator, comprising the steps of: supplying electrosurgical energy to tissue; determining a current of the electrosurgical energy; determining a log of the determined current of the electrosurgical energy; determining a voltage of the electrosurgical energy; determining a log of the determined voltage of the electrosurgical energy; and controlling the electrosurgical energy as a function of the log of the determined current and the log of the determined voltage.
 18. The method according to claim 17, further comprising the step of: applying a proportional-integral-derivative transfer function using at least one of the log of the determined current, the log of the determined voltage, a log impedance and a log power; and adjusting the electrosurgical energy as a function of the applied proportional-integral-derivative transfer function.
 19. The method according to claim 17, further comprising the step of adjusting a gain coefficient of the proportional-integral-derivative transfer function.
 20. The method according to claim 17, wherein the proportional-integral-derivative transfer function is applied to a comparison between a setpoint and at least one of the log of the determined current, the log of the determined voltage, the log impedance and the log power. 